CN102048554A - Radiographic apparatus - Google Patents
Radiographic apparatus Download PDFInfo
- Publication number
- CN102048554A CN102048554A CN2010105090843A CN201010509084A CN102048554A CN 102048554 A CN102048554 A CN 102048554A CN 2010105090843 A CN2010105090843 A CN 2010105090843A CN 201010509084 A CN201010509084 A CN 201010509084A CN 102048554 A CN102048554 A CN 102048554A
- Authority
- CN
- China
- Prior art keywords
- grid
- radiation
- image
- section
- shadow
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
Links
- 230000005855 radiation Effects 0.000 claims abstract description 229
- 239000011888 foil Substances 0.000 claims abstract description 75
- 238000003384 imaging method Methods 0.000 claims description 34
- 238000001514 detection method Methods 0.000 claims description 27
- 238000000034 method Methods 0.000 claims description 19
- 230000001360 synchronised effect Effects 0.000 claims description 19
- 238000009792 diffusion process Methods 0.000 claims description 16
- 239000011295 pitch Substances 0.000 claims description 15
- 230000008859 change Effects 0.000 claims description 5
- 230000000903 blocking effect Effects 0.000 claims description 2
- 230000003760 hair shine Effects 0.000 claims description 2
- 101100048473 Fowlpox virus (strain NVSL) UNG gene Proteins 0.000 description 61
- 238000002594 fluoroscopy Methods 0.000 description 14
- 210000004027 cell Anatomy 0.000 description 6
- 238000004519 manufacturing process Methods 0.000 description 6
- 238000004458 analytical method Methods 0.000 description 5
- 230000009471 action Effects 0.000 description 4
- 238000005452 bending Methods 0.000 description 4
- 230000007246 mechanism Effects 0.000 description 4
- 238000007689 inspection Methods 0.000 description 3
- 230000003321 amplification Effects 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 239000011159 matrix material Substances 0.000 description 2
- 238000003199 nucleic acid amplification method Methods 0.000 description 2
- 238000012935 Averaging Methods 0.000 description 1
- OKTJSMMVPCPJKN-UHFFFAOYSA-N Carbon Chemical compound [C] OKTJSMMVPCPJKN-UHFFFAOYSA-N 0.000 description 1
- 101000693735 Homo sapiens Prefoldin subunit 4 Proteins 0.000 description 1
- 229910001182 Mo alloy Inorganic materials 0.000 description 1
- 102100025542 Prefoldin subunit 4 Human genes 0.000 description 1
- 229910001362 Ta alloys Inorganic materials 0.000 description 1
- 238000010521 absorption reaction Methods 0.000 description 1
- 238000013459 approach Methods 0.000 description 1
- 210000003050 axon Anatomy 0.000 description 1
- 210000000988 bone and bone Anatomy 0.000 description 1
- 238000006073 displacement reaction Methods 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 229910002804 graphite Inorganic materials 0.000 description 1
- 239000010439 graphite Substances 0.000 description 1
- 238000010606 normalization Methods 0.000 description 1
- 230000008569 process Effects 0.000 description 1
- 210000001519 tissue Anatomy 0.000 description 1
- 230000009466 transformation Effects 0.000 description 1
- 210000001835 viscera Anatomy 0.000 description 1
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
- A61B6/5211—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data
- A61B6/5252—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data removing objects from field of view, e.g. removing patient table from a CT image
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/42—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis
- A61B6/4208—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
- A61B6/4233—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector using matrix detectors
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/42—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis
- A61B6/4291—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis the detector being combined with a grid or grating
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/44—Constructional features of apparatus for radiation diagnosis
- A61B6/4429—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units
- A61B6/4435—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units the source unit and the detector unit being coupled by a rigid structure
- A61B6/4441—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units the source unit and the detector unit being coupled by a rigid structure the rigid structure being a C-arm or U-arm
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
- A61B6/5258—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise
- A61B6/5282—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise due to scatter
-
- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
- G06T5/00—Image enhancement or restoration
- G06T5/50—Image enhancement or restoration by the use of more than one image, e.g. averaging, subtraction
-
- G—PHYSICS
- G21—NUCLEAR PHYSICS; NUCLEAR ENGINEERING
- G21K—TECHNIQUES FOR HANDLING PARTICLES OR IONISING RADIATION NOT OTHERWISE PROVIDED FOR; IRRADIATION DEVICES; GAMMA RAY OR X-RAY MICROSCOPES
- G21K1/00—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating
- G21K1/02—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators
- G21K1/025—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators using multiple collimators, e.g. Bucky screens; other devices for eliminating undesired or dispersed radiation
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/40—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis
- A61B6/4021—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis involving movement of the focal spot
-
- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
- G06T2207/00—Indexing scheme for image analysis or image enhancement
- G06T2207/10—Image acquisition modality
- G06T2207/10116—X-ray image
- G06T2207/10121—Fluoroscopy
-
- G—PHYSICS
- G21—NUCLEAR PHYSICS; NUCLEAR ENGINEERING
- G21K—TECHNIQUES FOR HANDLING PARTICLES OR IONISING RADIATION NOT OTHERWISE PROVIDED FOR; IRRADIATION DEVICES; GAMMA RAY OR X-RAY MICROSCOPES
- G21K2207/00—Particular details of imaging devices or methods using ionizing electromagnetic radiation such as X-rays or gamma rays
Abstract
In a radiographic apparatus, when a radiation source and the radiation detector are in a standard position, an arrangement pitch of shadows of absorbing foil strips appearing on a detecting plane of the radiation detector as a result of a radiation beam being emitted from the radiation source and blocked by the radiation grid is an integral multiple of an arrangement pitch in a transverse direction of radiation detecting elements. Further, positions of a radiation grid and a radiation detector are determined such that, the shadows of the absorbing foil strips appear without covering transversely adjacent pairs of the detecting elements.
Description
Technical field
The present invention relates to particularly possess the radiation imaging apparatus of the lonizing radiation grid that the diffusion lonizing radiation that produced by subject are removed by subject irradiation lonizing radiation being obtained the radiation imaging apparatus of perspective picture.
Background technology
In medical institutions, has the radiation imaging apparatus of taking the fluoroscopy images of subject by lonizing radiation.Such radiation imaging apparatus 51 as shown in figure 15, has the monitor station 52 of mounting subject M; The radiation source 53 of irradiation lonizing radiation; With the radiation detector 54 that detects lonizing radiation.
On the plane of incidence (detection faces) that the lonizing radiation of radiation detector 54 are injected, has the lonizing radiation grid 55 of having removed the diffusion lonizing radiation that produce by subject.Lonizing radiation grid 55 constitutes the absorbing foil of elongate and arranges in the mode of shutter.If this absorbing foil is run into the diffusion lonizing radiation, then most of lonizing radiation are absorbed paper tinsel and absorb, and are not injected into radiation detector 54.The diffusion lonizing radiation are absorbed and are removed by lonizing radiation grid 55.
By lonizing radiation grid 55 is set, can obtain the fluoroscopy images of the distinctness of having removed the diffusion lonizing radiation, and produce following problem on the other hand.That is: in radiation detector 54, mirror the shadow of absorbing foil.So, in fluoroscopy images, mirror the dark striped of pixel value, this makes the definition variation of fluoroscopy images.
In radiation imaging apparatus in the past, have and possess the device that removes the structure of this striped by Flame Image Process.That is, lonizing radiation device in the past carries out frequency analysis to fluoroscopy images and removes striped.The striped of mirroring in fluoroscopy images is the striped that many concealed wires are arranged with constant spacing, so if fluoroscopy images is carried out frequency analysis, then the striped component collects in certain fixed frequency.After the processing of removing this frequency component, carry out the frequency inverse transformation, then will obtain the fluoroscopy images of having removed striped.
The removal method of such striped also can be used in the lonizing radiation grid of synchronized model.Lonizing radiation grid at synchronized model describes.On the detection faces of radiation detector 54, with the rectangular detecting element that lonizing radiation are detected that is arranged with.A kind of lonizing radiation grid of synchronized model, be spacing with the shadow of the absorbing foil that in radiation detector 54, mirrors be the mode of integral multiple of the spacing of detecting element arrange absorbing foil made the lonizing radiation grid (with reference to the spy of Japan open the 2000-83951 communique, the spy opens the 2002-257939 communique).If on normal place, set radiation source and radiation detector and adopt synchronized model lonizing radiation grid, then since the spacing of the shadow of the spacing of detecting element and absorbing foil interfere and can not produce ripple, so can obtain the fluoroscopy images of the disorder of the image that further minimizing causes by the shadow of absorbing foil.Even adopt the lonizing radiation grid of synchronized model, also talkatively become not obvious, but with in fluoroscopy images, manifest striped and do not have differently, these stripeds are removed by frequency analysis.
Yet,, have following problem points according to radiation imaging apparatus in the past.
That is,, be difficult to remove fully the striped that manifests in the fluoroscopy images according to radiation imaging apparatus in the past.As shown in figure 15, supported by C arm 57 under the situation of radiation source 53 and radiation detector 54, by 57 rotations of C arm, radiation source 53 and radiation detector 54 can have a down dip at the state that keeps position each other.When adopting such radiation imaging apparatus to take, on one side C arm 57 is tilted, Yi Bian take.57 bendings of C arm only can make the relative position generation minor shifts of radiation source 53 and radiator 54.So the position of the shadow of the absorbing foil that manifests in the detection faces of radiation detector 54 can be moved.
Existing type lonizing radiation grid is arranged absorbing foil by pads such as clamping graphite between absorbing foil, and this pad also absorbs lonizing radiation to a certain extent.Under the situation of synchronized model lonizing radiation grid, what all is not provided with and forms hollow between adjacent absorbing foil, can reduce the absorption of lonizing radiation.On the other hand, because hollow structure, absorbing foil 55a has distortion and can not correctly form linearity.In a word, the shadow of the absorbing foil that the meeting projection is wriggled on the detection faces of radiation detector 54.Even so, the shadow of absorbing foil also is positioned at the horizontal central authorities of detecting element, does not cross in horizontal adjacent detecting element, and the shadow of absorbing foil is revealed as the ordinate of the width with a pixel part in fluoroscopy images.
According to this state, if make the C arm tilt to take, then the shadow of absorbing foil moves in the horizontal.So, because the shadow of absorbing foil wriggles, so shadow is partly from horizontal leap or do not cross over detecting element.So in fluoroscopy images, the shadow of absorbing foil is revealed as complicated striped.It is difficult removing such striped by frequency analysis.It is complicated that striped becomes, and is difficult to unify to remove by frequency analysis.
Summary of the invention
The present invention is in view of such situation, and its purpose is, provides a kind of shadow of absorbing foil that can be by mirroring the lonizing radiation grid in radiation detector to remove the radiation imaging apparatus of eclipsed striped in fluoroscopy images reliably.
The present invention is made as following structure in order to solve above-mentioned problem.
That is, radiation imaging apparatus of the present invention has: radiation source, and it shines lonizing radiation; Radiation detector, it has rectangular detection faces of having arranged the radiation detection device that lonizing radiation are detected; Image generation unit, its detection signal to be exported from described radiation detector generates image; The lonizing radiation grid, it is set to: show the absorbing foil that extends longitudinally along transverse row, and cover the detection faces of described radiation detector; The grid image memory element, it changes the horizontal position of described radiation source and described radiation detector under the state that stays out of subject between described radiation source and the described radiation detector on one side, carry out the shooting of described lonizing radiation grid on one side, and store many grid images of mirroring the shadow that described lonizing radiation grid is arranged; The raw image storage unit, it carries out the shooting of subject under the state of getting involved subject between described radiation source and the described radiation detector, and the original image of the shadow of the absorbing foil that the perspective of subject picture and described lonizing radiation grid are arranged is mirrored in storage; Selected cell among its a plurality of grid images of being stored, is selected the most similar grid image of pattern to the shadow of mirroring the described lonizing radiation grid in the original image in described grid image memory element; With the cancellation unit, it is based on by the selected grid image of selected cell, the shadow of the absorbing foil in the original image has been mirrored in cancellation, when described radiation source and described radiation detector are positioned at normal place, by blocking with described lonizing radiation grid from the radiation beam of described radiation source irradiation, thereby make the arrangement pitches of shadow of the absorbing foil that detection faces at described radiation detector manifests become the integral multiple of the horizontal arrangement pitches of radiation detection device, and, determine the position of described lonizing radiation grid and described radiation detector, so that the shadow of absorbing foil manifests not cross over the radiation detection device mode laterally adjacent with radiation detection device.
According to radiation imaging apparatus of the present invention, be provided with lonizing radiation grid with the synchronous synchronized model of the arrangement of the detecting element of radiation detector.That is, the arrangement pitches with radiation detection device is the arrangement pitches that the absorbing foil of lonizing radiation grid is decided on the basis.Thus, when the highest radiation source of usage frequency and radiation detector were positioned at normal place, the arrangement of the shadow of absorbing foil and the arrangement of radiation detection device interfered, and can not produce ripple, so can generate the higher radiation image of definition.
Yet, the lonizing radiation grid of such synchronized model, absorbing foil is easy to deform.As if the warpage of absorbing foil, then be difficult to predict the pattern of the shadow of the lonizing radiation grid that in original image, manifests, be difficult to from original image, remove the shadow of lonizing radiation grid.
At this, according to the present invention, taken a plurality of grid images in advance, select to original image in the most similar grid image of pattern of shadow of the lonizing radiation grid mirrored, and utilize it to come the pattern of the shadow of the lonizing radiation grid that cancellation mirrors in original image.According to the present invention, can predict the shadow of the lonizing radiation grid of in original image, having mirrored what shape, thereby from original image, remove the pattern of the shadow of lonizing radiation grid exactly.
In addition, in above-mentioned radiation imaging apparatus, the grid image of being stored in the more preferably described grid image memory element is on one side be that an edge laterally changes the image that described radiation detector is taken with respect to the position of described radiation source.
According to said structure, can take grid image more rightly.If the position of radiation source and radiation detector relation is along lateral shift, the pattern of the shadow of the lonizing radiation grid that then manifests in original image can great changes will take place.So in said structure, an edge laterally changes the position with respect to the radiation source of radiation detector, Yi Bian take grid image.According to such mode, even the position of radiation source and radiation detector relation is along lateral shift when obtaining original image, the pattern of the shadow of the lonizing radiation grid that manifests in original image also can be selected from the image that has photographed as grid image.Therefore, can predict the pattern of the shadow of the lonizing radiation grid that in original image, manifests exactly.
In addition, in above-mentioned radiation imaging apparatus, the grid image of being stored in the more preferably described grid image memory element is at what does not all photograph under the state of mounting between described radiation source and the described lonizing radiation grid image.
According to said structure, can take grid image more rightly.According to as above-mentioned structure, in grid image, only mirrored the shadow of lonizing radiation grids, so can show the pattern of the shadow of the lonizing radiation grid that manifests in the original image exactly.
In addition, in above-mentioned radiation imaging apparatus, the grid image of being stored in the described grid image memory element, can be in mounting between described radiation source and the described lonizing radiation grid produce the image that photographs under the state of the virtual image of diffusion lonizing radiation.
According to said structure, can take grid image more rightly.Comprise the component of the diffusion lonizing radiation that produced by subject in original image, the pattern of the shadow of the lonizing radiation grid that manifests in the original image also is subjected to the influence of diffusion lonizing radiation and changes.Therefore, under the state that produces the diffusion lonizing radiation, take the shadow that grid image can be understood the lonizing radiation grid that manifests in the original image more accurately sometimes.According to said structure, can obtain the grid image of the influence of having considered the diffusion lonizing radiation.
In addition, in above-mentioned radiation imaging apparatus, more preferably also have: the section generation unit, it is based on the image of two-dimensional arrangements pixel value, generate the section that pixel value is arranged along the horizontal string of described lonizing radiation grid, selected cell adopts the original image section that is generated by original image to reach the grid section that is generated by grid image and selects grid image.
Above-mentioned structure has showed the details of the system of selection of grid image.That is, the similar judgement of original image and grid image, be not adopt image himself, but adopt section that the feature of the shadow of the lonizing radiation grid mirrored in image is represented to carry out.Section is the section that pixel value is arranged by string, so can carry out the comparison between the section at high speed.Therefore, in the inspection of taking original image continuously, also can remove the shadow of the lonizing radiation grid of in original image, mirroring reliably.
In addition, in above-mentioned radiation imaging apparatus, more preferably described section generation unit is created on the section of inferring when not mirroring described lonizing radiation grid in the original image by the original image section, described radiation imaging apparatus is inferred section and is generated and relatively use section by deducting from the original image section, and selected cell is by selecting and relatively selecting grid image with the most similar grid section of section.
Above-mentioned structure has showed the details of the system of selection of grid image.That is, in original image, overlapped the shadow of subject picture and lonizing radiation grid.If the section of original image is directly used in comparison between the section, then the component of eclipsed subject picture can be upset the judgement of the similarity of section in the section of original image.The present invention constitutes in light of this situation: by the original image section be created on do not mirror in the original image subject as the time relatively use section, and by it being used for the similarity of relatively judging two sections with the grid section.Thus, can understand the shadow of the lonizing radiation grid of in original image, mirroring more reliably.
In addition, in above-mentioned radiation imaging apparatus, more preferably selected cell utilizes method of correlation to differentiate relatively to use the similarity of section and grid section.
Said structure has showed the concrete grammar of judgement of the similarity of two sections.If the method for correlation of the correlation coefficient by obtaining two sections compares, then can understand the shadow of the lonizing radiation grid of in original image, mirroring more reliably.
According to radiation imaging apparatus of the present invention, also has the synchronized model lonizing radiation grid of the distortion that is easy to produce absorbing foil.As if the warpage of absorbing foil, then be difficult to from original image, remove the shadow of lonizing radiation grid.So, according to the present invention, taken a plurality of grid images in advance, therefrom select appropriate grid image, and utilize selected grid image to come the pattern of the shadow of the lonizing radiation grid mirrored in the cancellation original image.According to the present invention, can from original image, remove the pattern of the shadow of lonizing radiation grid exactly.
In addition, in above-mentioned radiation imaging apparatus, more preferably have: the C arm, it supports described radiation source and described radiation detecting unit.
Above-mentioned structure has been represented concrete structure of the present invention.According to above-mentioned structure, can keep the position of radiation source and radiation detecting unit to concern to move both.
In addition, in above-mentioned radiation imaging apparatus, more preferably described lonizing radiation grid is the synchronous synchronous grid of arrangement of the detecting element of the arrangement of described absorbing foil and described radiation detector.
Above-mentioned structure has been represented concrete structure of the present invention.The present invention can be applicable to so-called synchronous grid.
Description of drawings
Fig. 1 is the functional-block diagram of structure of the X ray filming apparatus of explanation embodiment 1.
Fig. 2 A is the sketch map of mobile pattern of the C arm of explanation embodiment 1.
Fig. 2 B is the sketch map of mobile pattern of the C arm of explanation embodiment 1.
Fig. 3 is the axonometric chart of structure of the X ray grid of explanation embodiment 1.
Fig. 4 is the sketch map of position relation of X ray grid, FPD, the X-ray tube of explanation embodiment 1.
Fig. 5 is the axonometric chart of structure of the X ray grid of explanation embodiment 1.
Fig. 6 is the sketch map of acquisition methods of the grid image of explanation embodiment 1.
Fig. 7 is the sketch map of acquisition methods of the grid image of explanation embodiment 1.
Fig. 8 is the sketch map of the grid image of explanation embodiment 1.
Fig. 9 is the sketch map of the grid image of explanation embodiment 1.
Figure 10 is the sketch map of the grid section of explanation embodiment 1.
Figure 11 is the flow chart of the action of explanation embodiment 1.
Figure 12 A is the sketch map of the acquisition methods of relatively using section of explanation embodiment 1.
Figure 12 B is the sketch map of the acquisition methods of relatively using section of explanation embodiment 1.
Figure 12 C is the sketch map of the acquisition methods of relatively using section of explanation embodiment 1.
Figure 13 is the sketch map of the original image of explanation embodiment 1.
Figure 14 is the sketch map of an explanation variation of the present invention.
Figure 15 is the functional-block diagram of structure of the X ray filming apparatus of explanation existing structure.
The specific embodiment
Below, embodiments of the invention are described.X ray among the embodiment is equivalent to lonizing radiation of the present invention.
The structure of＜X ray filming apparatus 〉
Position relation at FPD4 and X ray grid 5 describes.Fig. 4 represents the relation of X ray grid 5 and FPD4 and X-ray tube 3.X ray Dx is radiated from the focus P of X-ray tube 3.Be arranged in parallel though the absorbing foil 5a of Fig. 3 looks like, be actually in mode and angle is changed and arrange along the X ray Dx that is radiated.The FPD4 that the shadow S that makes absorbing foil 5a is appeared before one's eyes in the central authorities of the detecting element 4a of FPD4 and the position relation of X-ray tube 3 are called normal place.
On the detection faces of the X ray that detects FPD4, as shown in Figure 5, be arranged with the detecting element 4a that detects X ray in length and breadth.If from X-ray tube 3 irradiation X ray, then the shadow S of the absorbing foil 5a of X ray grid 5 can be mirrored in any of detecting element 4a of FPD4.At this moment, shadow S can come the horizontal central authorities of certain detecting element 4a as shown in Figure 5.Therefore, the shadow S of absorbing foil 5a be revealed as not cross over detecting element 4a at horizontal adjacent detecting element 4a.And the horizontal arrangement pitches of shadow S becomes the integral multiple (being 4 times in an embodiment) of arrangement pitches of the detecting element 4a of FPD4.So, the arrangement pitches transversely of the position of the absorbing foil 5a on the FPD4 and absorbing foil 5a, respectively with the position of shadow S and detecting element 4a, and the horizontal arrangement pitches of each detecting element 4a determine as benchmark.X ray grid 5 after the arrangement pitches that makes the arrangement pitches of such absorbing foil 5a and detecting element 4a matched is called synchronous X ray grid.Detecting element 4a is equivalent to radiation detection device of the present invention.
But, as shown in Figure 2, if C arm 7 rotation, then the shadow S of the absorbing foil 5a of X ray grid 5 can be from the horizontal central offset of the detecting element 4a of FPD4.X-ray tube 3 is weights, if support it by C arm 7, then C arm 7 can be crooked.This bending is along with X-ray tube 3 leaves and becomes big from pillar 8.FPD4 and shadow S become the state as Fig. 5, be when as shown in Figure 1 X-ray tube 3 be positioned at FPD4 just under state the time.
In addition, though by FPD travel mechanism 23 make FPD4 and X-ray tube 3 approaching/deviate from, the shadow of the absorbing foil 5a of X ray grid 5 also can be from the horizontal central offset of the detecting element 4a of FPD4.This be because if make FPD4 and X-ray tube 3 approaching/deviate from, then the amplification of the X ray grid 5 on the FPD4 is understood change.FPD4 and shadow S become the such state of Fig. 5, be when X-ray tube 3 and FPD4 be in specified standard apart from the time.
In addition, the X ray filming apparatus 1 of embodiment 1 has as shown in Figure 1: the image production part 11 that generates various images; Generate the section generating unit 12 of relatively using section c; Select one grid image selection portion 13 among the grid image G; The cancellation portion 14 of the shadow of the X ray grid 5 that removal is mirrored in original image P0; Make the operating board 31 of the indication input of surgical doctor; The display part 32 that shows correcting image; Information storage part 33 with storing various information.Cancellation portion 14 is equivalent to cancellation of the present invention unit, and image production part 11 is equivalent to image generation unit of the present invention.In addition, section generating unit 12 is equivalent to section generation unit of the present invention, and grid image selection portion 13 is equivalent to selected cell of the present invention.In addition, information storage part 33 is equivalent to grid image memory element of the present invention, raw image storage unit.
In addition, the X ray filming apparatus 1 among the embodiment 1 has the master control part 34 that each one 6,11,12,13,14,22,24 is unified to control.Master control part 34 is made of CPU, realizes each one by carrying out various programs.In addition, above-mentioned each one also can be divided into the arithmetic unit of taking on them and carries out.
G describes at grid image.Grid image G takes with X ray to be set at the image that obtains behind the X ray grid 5 of FPD4, stores 189 in information storage part 33.This grid image G obtains under the state that takes off X-ray tube 3 and PFD4 from C arm 7.That is, by obtaining grid image G towards the FPD4 irradiation X ray that X ray grid 5 is installed.
Image pickup method at grid image G describes.When taking grid image G, the X-ray tube 3 of irradiation X ray, as shown in Figure 6, by mounting in the platform 25 that laterally moves that makes X-ray tube 3 along X ray grid 5.Like this, can make X-ray tube 3, move along horizontal with respect to FPD4 from the state that X-ray tube 3 and FPD4 are positioned at normal place.In addition, that platform 25 can make X-ray tube is 3 approaching/deviate from FPD4.Therefore, can make X-ray tube 3 be positioned at the state of normal place from X-ray tube 3 and FPD 4, carry out with respect to FPD4 approaching/deviate from.So, the platform 25 of mounting X-ray tube 3 becomes the XY platform that can move along orthogonal both direction.
Describe at the situation of taking grid image G.In order to take grid image G, at first, from X-ray tube 3 irradiation X ray.So the shadow of X ray grid 5 is mirrored FPD4.Image production part 11 receives by FPD4 and detects data, and generates the grid image G of the shadow of having mirrored X ray grid 5.This grid image G is stored in the information storage part 33.
Such shooting is through repeatedly carrying out in the horizontal slip X-ray tube 3 in edge.That is, X-ray tube 3 along laterally moving, after temporarily stopping, carrying out the shooting of X ray grid 5 with platform once more.By repeating moving and taking of such X ray grid 5, take grid image G one by one.
How X-ray tube 3 when taking grid image G to be moved describe.Both position relation when Fig. 6 represents that X-ray tube 3 and FPD4 are positioned at normal place.Symbol P among the figure, the focus of the X ray beam that sends of expression X-ray tube 3.Because the shooting of grid image G is to carry out one by one when X-ray tube 3 is moved, so also change one by one at the position of the focus of the X-ray tube 3 of FPD4.
The focal position of the X-ray tube 3 of the time point of shooting X ray grid image G is any among P11～P47 as shown in Figure 7.In order to take the X ray grid image, at first, Yi Bian the focus that makes X-ray tube 3 from the normal place shown in the P24 along laterally moving, Yi Bian carry out the shooting of seven focal positions shown in the A2 of Fig. 7.Afterwards, with respect to FPD4 near after the focus of X-ray tube 3, an edge laterally moves and takes on one side, the X ray grid image of shooting on each focal position of the P11～P17 shown in the A1 of Fig. 7.Similarly, after the focus that has deviated from X-ray tube 3 with respect to FPD4, take, take the X ray grid image on seven focal positions of each shown in A3, the A4 of Fig. 7 Yi Bian an edge laterally moves.And, in Fig. 7, with the succinct purpose that is illustrated as, through four layers of shooting of having carried out at seven focal positions, and at adding up to 28 focal position to carry out the shooting of X ray grid image, but as the operation of the reality of embodiment 1, by the shooting of carrying out at nine focal positions through 21 layers, thereby at adding up to 189 focal position to carry out the shooting of X ray grid image.
Carry out simple explanation at the X ray grid image G that gets access to.When X-ray tube 3 is positioned at normal place (when the focus of X-ray tube 3 is positioned at the P24 of Fig. 7), the shadow S of absorbing foil shown in the left side of Fig. 8, is mirrored FPD4.Among the X ray grid image G of this moment, shown in the right side of Fig. 8, manifest the concealed wire of width with a pixel part.Yet, because the distortion that has of absorbing foil, the bending that has, so also distortion to a certain extent of its shadow S.For example, because absorbing foil 5a distortion, the horizontal width of shadow S is inconsistent.Influenced by this, in the concealed wire that in X ray grid image G, occurs, shown in the right side of Fig. 8, manifest the speckle that has part dark.
If move X-ray tube 3 from normal place, then the shadow S of absorbing foil shown in the left side of Fig. 9, is mirrored FPD4 from the state of Fig. 8 along laterally moving.The shadow S of absorbing foil is owing to be the shape of distortion, so shadow S is partly from horizontal leap or do not cross over detecting element 4a.Among the X ray grid image G at this moment, shown in the right side of Fig. 9, manifest the concealed wire that is complicated shape.In the part that shadow S has crossed over detecting element 4a, shadow S is assigned in horizontal adjacent detecting element 4a, in X ray grid image G, manifests the concealed wire of the width with two pixel parts.In the part that shadow S does not cross over detecting element 4a, the width of the concealed wire that manifests among the X ray grid image G keeps original pixel part.
X ray grid image G, by image production part 11, X-ray tube 3 when being endowed with shooting and the position of FPD4 concern after the relevant information, are sent to section generating unit 12.The X ray grid image G that section generating unit 12 will become two dimensional image is transformed to one-dimensional data.That is, section generating unit 12, as shown in figure 10, among the pixel value that constitutes X ray grid image G, the pixel value that string is longitudinally arranged averages, and generates along the transversely arranged grid section g of meansigma methods.As other method of generating mesh section g, also can extract the pixel value group that horizontal string is arranged out at certain position longitudinally of the X ray grid image G shown in the arrow a of Figure 10.Section generating unit 12, make X ray grid image G with based on it and the generation grid section g be stored in explicitly in the information storage part 33.So, in information storage part 33,28 (actual is 189) X ray grid image G and grid section g set up related the storage.
The action of＜X ray filming apparatus 〉
Then, the action at the X ray filming apparatus describes.For the X ray filming apparatus with embodiment 1 is checked, at first, as shown in figure 11, take X ray grid 5 in advance, and get access to a plurality of grid image G (grid is taken step S1).Then, under the state of mounting subject M on the monitor station, carry out the shooting of subject M and obtain original image P0 (subject is taken step S2), and, obtain and relatively use section c (relatively generating step S3) with section c based on original image P0.Then, compare relatively using section c and grid image G (accurately is its cross-sectional data), select to original image P0 in the most similar grid image G (grid image selection step S4) of striped of shadow of the X ray grid 5 mirrored.At last, adopt selected grid image G to come the striped (cancellation step S5) of the shadow of the X ray grid 5 that cancellation mirrors in original image P0.Below, each step at them describes in order.
＜grid is taken step S1, and subject is taken step S2 〉
At first, with X-ray tube 3 mountings under the state of platform, carry out the shooting of X ray grid 5.This step can be carried out once before the X ray filming apparatus dispatches from the factory.Therefore, the inspection of actual subject M is from mounting subject M on monitor station 2, and begins (subject is taken step S2) when subject M irradiation X ray beam.FPD4 detects the X ray beam that sees through subject M, detects data and is sent to image production part 11.Image production part 11 will detect data and carry out two-dimensional arrangements etc., obtain to mirror the original image P0 that the perspective of subject M picture and the shadow of X ray grid 5 are arranged.
＜relatively generate step S3 with section: generate original image section p 〉
Original image P0 is sent to section generating unit 12.Section generating unit 12 is original image section p with the section that generates original image P0 with the identical main points of generating mesh section g.Original image section p is by averaging pixel value or releasing from the pixel value group that the horizontal string of original image P0 is arranged and obtain.Original image section p, shown in Figure 12 A epimere, component that becomes overlapping to form with the shadow S of the absorbing foil shown in the oblique line and the component that forms with the perspective picture of the subject M shown in the shade the two.
＜relatively generate step S3 with section: extract regional A out 〉
The reason that only comprises the component of subject picture at regional A describes.Figure 13 is the sketch map of the shadow of the absorbing foil that occurs among the original image P0.When X-ray tube 3 was positioned at normal place with FPD4, the shadow S of absorbing foil shown in the upside of Figure 13, was apparent in the area B of the width of a pixel part.If area B with original image P0 on the whole, then is striated along laterally manifesting repeatedly.And, in Figure 13, component that becomes overlapping to form with the shadow S of the absorbing foil shown in the oblique line and the component (component of subject picture) that forms with the perspective picture of the subject M shown in the shade the two.With the perspective picture of the subject M shown in the shade, be actually the viscera tissue of subject M or osseous tissue etc.
If X-ray tube 3 is offset from normal place with the relative position of FPD4, then shown in the downside of Figure 13, the shadow S of absorbing foil can overflow and manifests from area B.But, in regional A shown in Figure 13, can not manifest the shadow S of absorbing foil.How no matter X-ray tube 3 changes if closing in the shooting that ties up to subject M with the position of FPD4, the horizontal displacement of the shadow S of the absorbing foil among the original image P0 is less than the distance of a pixel part, and the shadow S of absorbing foil does not move to from area B along laterally leaving the regional A of two pixel parts.
Describe at this reason.Because the bending of C arm 7, X-ray tube 3 is about 2mm with the deviation of the position of FPD4.From the distance the X-ray tube 3 to FPD4, normal place is about 1000mm, and X ray grid 5 is 20mm with the distance of FPD4.According to these, the relative position by X-ray tube 3 and FPD4 is at the transversely change 2mm of X ray grid 5, thereby the shadow S of absorbing foil is along laterally moving 40 μ m.The horizontal width of the shadow S of absorbing foil, though more or less change, but be about 30 μ m, the horizontal width of the detecting element 4a that the detection faces of FPD4 is arranged is 100 μ m, so, the shadow S of the absorbing foil that exists in the area B of original image P0 moves to away from the regional A more than the 100 μ m, can be described as impossible.
＜relatively generate step S3 with section: generate hypothesis section sp 〉
＜relatively generate step S3 with section: generate and relatively use section c
＜grid image is selected step S4 〉
Relatively be sent to grid image selection portion 13 with section c.This relatively is illustrated in the pattern of the shadow of the X ray grid of mirroring among the original image P0 5 with section c.In information storage part 33, should exist and the grid section g that relatively uses section c identical patterns.Grid image selection portion 13 is selected the grid section g the most similar to the pattern of relatively using section c.
Describe at the detailed action of selecting grid section g.Grid image selection portion 13 at first, is carried out selecting of grid image G roughly.In this grid image selection portion 13,, send the range information of X-ray tube 3 and FPD4 by FPD mobile control division 24.Selecting near among the A1～A4 among Fig. 7 any when 13 pairs of grid image selection portions are taken original image P0 with respect to the position of the X-ray tube 3 of FPD4.At this moment, for example, grid image selection portion 13 has been selected A1.Grid image selection portion 13 is read the focus of X-ray tube 3 seven the X ray grid image Gs captured in the A1 position (being its grid section g accurately) from information storage part 33.
So grid image selection portion 13 by comparing two section g, c, is selected an X ray grid image G from seven X ray grid image G.Particularly, the grid section g of seven X ray grid image G is acted on successively relatively use section c, obtain correlation coefficient h, select grid image G.This correlation coefficient h is expression grid section g and the index of relatively using the consistent degree of section c.Correlation coefficient h is high more, and two sections are consistent more.Grid section g and relatively represented the pattern of the shadow of the X ray grid 5 that manifested among grid image G and the original image P0 with section c.Therefore, the correlation coefficient h height of so-called two sections has represented that the pattern of shadow of the X ray grid 5 that manifested is similar to the pattern of the shadow of the X ray grid 5 that is manifested in original image P0 in grid image G.
Acquisition methods at the correlation coefficient h of grid image selection portion 13 describes.The pixel value of grid section g is that horizontal string is arranged, so can represent grid section g with following matrix.
g＝{g
1，g
2，…g
n?}
Similarly, also be that the horizontal string of pixel value is arranged relatively, so can represent relatively to use section c with following matrix with section c.
c＝{c
1，c
2，…c
n}
Grid image selection portion 13 calculates correlation coefficient h by following formula.Correlation coefficient h is a scalar value.
h＝(g
1c
1+g
2c
2+…g
n?c
n)
/(g
1 2+g
2 2+…+g
n 2)
1/2·(c
1 2+c
2 2+…+c
n 2)
1/2
Grid image selection portion 13 at seven grid section g, is obtained correlation coefficient respectively.So grid image selection portion 13 is selected the grid section g of correlation coefficient g maximum, and selects the grid image G corresponding with it.Thus, grid image selection portion 13 is selected: among grid image G, to the most similar pattern of pattern of the shadow of the X ray grid of mirroring in original image P0 5.Correlation coefficient h is the value that obtains after the scalar product of two section g, the c value divided by regulation.The denominator of this moment is the denominator that is provided with for the normalization of the value of scalar product.
Then, the concrete example of expression correlation coefficient h.For example, if two section g, c are identical, then the value of correlation coefficient is 1.In addition, along with two section g, c are inconsistent, correlation coefficient h approaches 0.To adopt such correlation coefficient h to judge that the method for the similarity of image is called method of correlation.Hypothetical trellis image selection portion 13 has been selected grid image Ga in grid image G, to carry out the following description.
＜cancellation step S5 〉
Grid image selection portion 13 sends to cancellation portion 14 with selected grid image Ga.Cancellation portion 14 overlaps the inversion pattern of grid image Ga with original image P0, generate from original image P0 the correcting image P1 after the pattern of the shadow of X ray grid 5 removed thus.In grid image Ga, owing to mirrored the identical pattern of pattern with the shadow of the X ray grid 5 that is overlapped in original image P0, so if they are overlapped, then the shadow of the X ray grid 5 among the original image P0 can be by cancellation exactly.In display part 32, show this correcting image P1, check and finish.
As mentioned above, according to the X ray filming apparatus 1 of embodiment 1, be provided with the synchronous synchronized model X ray grid 5 of arrangement with the detecting element 4a of FPD4.The arrangement pitches of the absorbing foil 5a of X ray grid 5 is that the basis is decided with the arrangement pitches of detecting element 4a.Thus, at the highest normal place place of usage frequency, the arrangement of the arrangement of the shadow of absorbing foil 5a and detecting element 4a interferes and can not produce ripple, so can generate the higher radioscopic image of definition.
Yet such synchronized model X ray grid 5 is easy to generate the distortion of absorbing foil 5a.If the shape of absorbing foil 5a deforms, then be difficult to predict the pattern of the shadow of the X ray grid 5 that manifests among the original image P0, and be difficult to from original image P0, remove the shadow of X ray grid 5.
So, the structure of embodiment 1, be after having taken a plurality of grid image G in advance, select to original image P0 in the most similar grid image G of pattern of shadow of the X ray grid 5 mirrored, and utilize it to come the pattern of the shadow of the X ray grid 5 mirrored among the cancellation original image P0.In a word,, in knowing original image P0 in advance, mirrored on the basis of shadow of X ray grid 5 of what shape, can from original image P0, remove the pattern of the shadow of X ray grid 5 exactly according to the structure of embodiment 1.
In addition, according to the structure of embodiment 1, can take grid image G more rightly.X-ray tube 3 is offset as if producing in the horizontal with the position relation of FPD4, and the pattern of the shadow of the X ray grid 5 that then manifests in original image P0 can great changes will take place.Therefore, in said structure, an edge laterally changes the position with respect to the FPD4 of X-ray tube 3, Yi Bian take grid image G.If so, when original image obtained, even the position of X-ray tube 3 and FPD4 relation produces skew in the horizontal, the pattern of the shadow of the X ray grid 5 that manifests among the original image P0 also had been the image that has been taken into grid image G.Therefore, can predict the pattern of the shadow of the X ray grid 5 that in original image P0, manifests exactly.
So,, can take grid image G more rightly according to the structure of embodiment 1.If as embodiment 1, between X-ray tube 3 and FPD4, except X ray grid 5, stay out of anything and take grid image G, the shadow of then only mirroring X ray grid 5 in grid image G is so can be illustrated in the pattern of the shadow of the X ray grid 5 that manifests among the original image P0 exactly.
In addition, according to the structure of embodiment 1, the similar judgement of original image P0 and grid image G, be not adopt image himself, but adopt the section of the feature of the shadow of having represented the X ray grid 5 in image, mirrored to carry out.The pixel value of the section of embodiment 1 is that string is arranged, so the comparison between the section can be to carry out at a high speed.Therefore, in the inspection of taking original image P0 continuously, also can remove the shadow of the X ray grid of in original image P0, mirroring 5 reliably.
Yet in original image P0, the subject picture overlaps with the shadow of X ray grid 5.If the section of original image P0 is directly used in comparison between the section, then the component of eclipsed subject picture can be upset the judgement of the similarity of section in the section of original image P0.Embodiment 1 in light of this situation, and form following structure: according to original image section p generate do not mirror among the original image P0 subject as the time relatively use section c, by it being used for the comparison with grid section g, generate the shadow of judging the X ray grid of mirroring among the original image P0 5 and the similarity of grid image G.Thus, can understand the shadow of the X ray grid of in original image P0, mirroring 5 more reliably.
In addition, if as described in the embodiment 1, the method for correlation of the correlation coefficient by obtaining two sections compares, and then can understand the shadow of the X ray grid of mirroring in original image P0 5 more reliably.
The present invention shown in the explanation of carrying out with Fig. 7, can be applicable to the situation of the distance of FPD4 and X-ray tube 3 than the distance of the normal place that is equivalent to Fig. 4, also can be applicable to short situation.
The present invention is not limited to the structure of the foregoing description, can implement distortion as described below.
(1) in embodiment 1, though between X-ray tube 3 and the FPD4 not the thing of mounting except X ray grid 5 take grid image G, the present invention is not limited to this structure.As shown in figure 14, can between X-ray tube 3 and FPD4, take grid image G by the tabular virtual image (phantom) Ph of mounting generation diffusion lonizing radiation.In original image P0, comprise the component of the diffusion lonizing radiation that produce by subject M, the pattern of the shadow of the X ray grid 5 that manifests in original image P0 also is subjected to the influence of diffusion lonizing radiation and changes.Therefore, under the state that produces the diffusion lonizing radiation, take grid image G more can understand the X ray grid 5 that manifests sometimes exactly in original image P0 shadow.According to the structure of this variation, can obtain the grid image G of the influence of having considered the diffusion lonizing radiation.
(2) in the above-described embodiments, in X ray filming apparatus 1, be provided with single C arm 7, but the present invention is not limited to this.The present invention also goes for being provided with the both arms type system of two C arms 7.
(3) the foregoing description, though be medical device, the present invention also can be applicable to device industrial or that nuclear power is used.
(4) the said X ray of the foregoing description is an example of the lonizing radiation among the present invention.Therefore, the present invention also can be applicable to X ray lonizing radiation in addition.
※ the present invention only otherwise break away from its thought or essence just can be implemented with other concrete form, therefore, as representing scope of invention, be not limited to above explanation, and will be with reference to additional technical scheme.
Claims (9)
1. a radiation imaging apparatus is used to obtain radiation image, and described radiation imaging apparatus comprises:
Radiation source, it shines lonizing radiation;
Radiation detector, it has the detection faces of having arranged the radiation detection device that lonizing radiation are detected with rectangular;
Image generation unit, its detection signal to be exported from described radiation detector generates image;
The lonizing radiation grid, it is set to: show the absorbing foil that extends longitudinally along transverse row, and cover the detection faces of described radiation detector;
The grid image memory element, it changes the horizontal position of described radiation source and described radiation detector under the state that stays out of subject between described radiation source and the described radiation detector on one side, carry out the shooting of described lonizing radiation grid on one side, and store many grid images of mirroring the shadow that described lonizing radiation grid is arranged;
The raw image storage unit, it carries out the shooting of subject under the state of getting involved subject between described radiation source and the described radiation detector, and the original image of the shadow of the absorbing foil that the perspective of subject picture and described lonizing radiation grid are arranged is mirrored in storage;
Selected cell among its a plurality of grid images of being stored, is selected the most similar grid image of pattern to the shadow of mirroring the described lonizing radiation grid in the original image in described grid image memory element; With
The cancellation unit, it is based on by the selected grid image of selected cell, and the shadow of the absorbing foil in the original image has been mirrored in cancellation,
When described radiation source and described radiation detector are positioned at normal place, by blocking with described lonizing radiation grid from the radiation beam of described radiation source irradiation, thereby make the arrangement pitches of shadow of the absorbing foil that detection faces at described radiation detector manifests become the integral multiple of the horizontal arrangement pitches of radiation detection device, and, determine the position of described lonizing radiation grid and described radiation detector, so that the shadow of absorbing foil manifests in the mode of not crossing over the radiation detection device laterally adjacent with radiation detection device.
2. radiation imaging apparatus according to claim 1 is characterized in that,
The grid image of being stored in the described grid image memory element is on one side be the laterally image that photographs with respect to the position of described radiation source of the described radiation detector of change of an edge.
3. radiation imaging apparatus according to claim 1 is characterized in that,
The grid image of being stored in the described grid image memory element is at what does not all photograph under the state of mounting between described radiation source and the described lonizing radiation grid image.
4. radiation imaging apparatus according to claim 1 is characterized in that,
The grid image of being stored in the described grid image memory element, be in mounting between described radiation source and the described lonizing radiation grid produce the image that photographs under the state of the virtual image of diffusion lonizing radiation.
5. radiation imaging apparatus according to claim 1 is characterized in that,
Described radiation imaging apparatus also has: the section generation unit, its based on two-dimensional arrangements the image of pixel value, generate the section that pixel value is arranged along the horizontal string of described lonizing radiation grid,
Selected cell adopts the original image section that is generated by original image to reach the grid section that is generated by grid image and selects grid image.
6. radiation imaging apparatus according to claim 5 is characterized in that,
Described section generation unit is created on the section of inferring when not mirroring described lonizing radiation grid in the original image by the original image section,
Described radiation imaging apparatus is inferred section and is generated and relatively use section by deducting from the original image section,
Selected cell is by selecting and relatively selecting grid image with the most similar grid section of section.
7. radiation imaging apparatus according to claim 6 is characterized in that,
Described selected cell utilizes method of correlation to differentiate relatively to use the similarity of section and grid section.
8. according to the described radiation imaging apparatus of claim 1～7, it is characterized in that,
Also have: the C arm, it is used to support described radiation source and described radiation detecting unit.
9. according to the described radiation imaging apparatus of claim 1～7, it is characterized in that,
Described lonizing radiation grid is the synchronous synchronous grid of arrangement of the detecting element of the arrangement of described absorbing foil and described radiation detector.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2009256963A JP5407774B2 (en) | 2009-11-10 | 2009-11-10 | Radiography equipment |
| JP2009-256963 | 2009-11-10 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN102048554A true CN102048554A (en) | 2011-05-11 |
| CN102048554B CN102048554B (en) | 2013-06-05 |
Family
ID=43953598
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201010509084.3A Expired - Fee Related CN102048554B (en) | 2009-11-10 | 2010-10-12 | Radiographic apparatus |
Country Status (3)
| Country | Link |
|---|---|
| US (1) | US8284902B2 (en) |
| JP (1) | JP5407774B2 (en) |
| CN (1) | CN102048554B (en) |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103784152A (en) * | 2012-11-01 | 2014-05-14 | 南京普爱射线影像设备有限公司 | C-shaped arm X-ray machine mechanical parameter analysis method |
| CN112308119A (en) * | 2020-10-15 | 2021-02-02 | 中国医学科学院北京协和医院 | Immunofluorescence classification method and device for glomerulonephritis |
Families Citing this family (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP5375655B2 (en) * | 2010-02-18 | 2013-12-25 | 株式会社島津製作所 | Radiography equipment |
| JP5482640B2 (en) * | 2010-12-13 | 2014-05-07 | 株式会社島津製作所 | Synchronous grid foil shadow removal method and radiation imaging apparatus using the same |
| WO2013140445A1 (en) * | 2012-03-21 | 2013-09-26 | 株式会社島津製作所 | Radiographic apparatus |
| JP5939163B2 (en) * | 2013-01-07 | 2016-06-22 | 株式会社島津製作所 | Radiography equipment |
| JP6006193B2 (en) * | 2013-03-28 | 2016-10-12 | 富士フイルム株式会社 | Radiation image processing apparatus and method, and program |
| CN104636707B (en) * | 2013-11-07 | 2018-03-23 | 同方威视技术股份有限公司 | The method of automatic detection cigarette |
| KR101684730B1 (en) * | 2014-02-25 | 2016-12-08 | 고려대학교 산학협력단 | Digital radiation detector |
| US9508127B1 (en) * | 2015-06-30 | 2016-11-29 | Konica Minolta Laboratory U.S.A., Inc. | Processing for creating a transmission image without artificial noises |
| KR102229064B1 (en) * | 2019-05-20 | 2021-03-19 | 주식회사 디알텍 | Radiation imaging apparatus and radiation imaging method using the same |
| JP2022092421A (en) * | 2020-12-10 | 2022-06-22 | キヤノンメディカルシステムズ株式会社 | X-ray diagnostic apparatus |
Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5050198A (en) * | 1989-03-09 | 1991-09-17 | Kabushiki Kaisha Toshiba | Method and system for processing X-ray image in X-ray equipment |
| CN1384661A (en) * | 2001-05-01 | 2002-12-11 | 佳能株式会社 | Radiation image processing equipment and method, image processing system, storing medium and program |
| CN101158653A (en) * | 2007-11-16 | 2008-04-09 | 西北工业大学 | Diffuse transmission measuring and correcting method of cone-beam CT system |
| CN101453954A (en) * | 2006-05-31 | 2009-06-10 | 株式会社岛津制作所 | Radiation image pick-up device |
Family Cites Families (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH06154207A (en) * | 1992-11-18 | 1994-06-03 | Canon Inc | Radiographic apparatus and positioning method thereof |
| JP3459745B2 (en) * | 1997-03-27 | 2003-10-27 | キヤノン株式会社 | Image processing apparatus, radiation imaging apparatus, and image processing method |
| JP3277866B2 (en) * | 1997-11-11 | 2002-04-22 | 株式会社島津製作所 | X-ray diagnostic equipment |
| JP2000083951A (en) | 1998-09-11 | 2000-03-28 | Canon Inc | X-ray radiographic device and grid device |
| US6826256B2 (en) * | 2000-02-04 | 2004-11-30 | Canon Kabushiki Kaisha | Apparatus and method for a radiation image through a grid |
| JP2002257939A (en) | 2001-03-06 | 2002-09-11 | Shimadzu Corp | Two-dimensional radiation detector, method of manufacturing it, and method of correcting it |
| JP3724393B2 (en) * | 2001-07-26 | 2005-12-07 | 株式会社島津製作所 | X-ray equipment |
| JP4497837B2 (en) * | 2003-05-12 | 2010-07-07 | キヤノン株式会社 | Radiation imaging equipment |
| JP4337450B2 (en) * | 2003-07-15 | 2009-09-30 | 株式会社島津製作所 | Radiation imaging apparatus and radiation detection signal processing method |
| JP2008538293A (en) * | 2004-11-24 | 2008-10-23 | コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ | Computer tomography method and computer tomography apparatus |
-
2009
- 2009-11-10 JP JP2009256963A patent/JP5407774B2/en not_active Expired - Fee Related
-
2010
- 2010-10-12 CN CN201010509084.3A patent/CN102048554B/en not_active Expired - Fee Related
- 2010-10-29 US US12/915,189 patent/US8284902B2/en not_active Expired - Fee Related
Patent Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5050198A (en) * | 1989-03-09 | 1991-09-17 | Kabushiki Kaisha Toshiba | Method and system for processing X-ray image in X-ray equipment |
| CN1384661A (en) * | 2001-05-01 | 2002-12-11 | 佳能株式会社 | Radiation image processing equipment and method, image processing system, storing medium and program |
| CN101453954A (en) * | 2006-05-31 | 2009-06-10 | 株式会社岛津制作所 | Radiation image pick-up device |
| CN101158653A (en) * | 2007-11-16 | 2008-04-09 | 西北工业大学 | Diffuse transmission measuring and correcting method of cone-beam CT system |
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103784152A (en) * | 2012-11-01 | 2014-05-14 | 南京普爱射线影像设备有限公司 | C-shaped arm X-ray machine mechanical parameter analysis method |
| CN103784152B (en) * | 2012-11-01 | 2016-01-13 | 南京普爱射线影像设备有限公司 | A kind of C-arm X-ray machine mechanical movement parameters analysis method |
| CN112308119A (en) * | 2020-10-15 | 2021-02-02 | 中国医学科学院北京协和医院 | Immunofluorescence classification method and device for glomerulonephritis |
| CN112308119B (en) * | 2020-10-15 | 2021-11-05 | 中国医学科学院北京协和医院 | Immunofluorescence classification method and device for glomerulonephritis |
Also Published As
| Publication number | Publication date |
|---|---|
| CN102048554B (en) | 2013-06-05 |
| US8284902B2 (en) | 2012-10-09 |
| JP5407774B2 (en) | 2014-02-05 |
| JP2011101686A (en) | 2011-05-26 |
| US20110110500A1 (en) | 2011-05-12 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN102048554B (en) | Radiographic apparatus | |
| CN102264301B (en) | Radiation imaging device | |
| CN101836867B (en) | Radiographic apparatus | |
| US20170205360A1 (en) | X-ray imaging system allowing the correction of the scatter radiation and precise detection of the distance between the source and the detector | |
| EP1408450A2 (en) | Automatic arrangement determination of partial radiation images for reconstructing a stitched full image | |
| JP2012045278A (en) | X-ray imaging apparatus and x-ray imaging method | |
| JP7164524B2 (en) | X-ray CT device | |
| EP2509501A1 (en) | Phase contrast imaging | |
| CN102770075B (en) | X-ray image diagnosis device, and medical image processing method | |
| US20170100088A1 (en) | Iterative reconstruction process | |
| JP5804340B2 (en) | Radiation image region extraction device, radiation image region extraction program, radiation imaging device, and radiation image region extraction method | |
| JP2005013738A (en) | System and method for scanning object in tomosynthesis application | |
| US20140301625A1 (en) | Image processing apparatus and radiographic apparatus having the same | |
| JP6683118B2 (en) | X-ray phase imaging device | |
| CN102711616A (en) | Radiation tomography device | |
| CN102113891B (en) | Radiation-ray camera pick-up device | |
| JP2020127708A (en) | Correction based on learning of grid artifact in x-ray imaging | |
| CN107495978A (en) | X-ray shooting system and image-pickup method | |
| JP2013000261A (en) | Radiographic device | |
| JP2023088704A (en) | Radioactive imaging device, method for generating image, radioactive imaging system, and program | |
| US9616250B2 (en) | Treatment system, control device and treatment method | |
| KR20190028305A (en) | Image processing apparatus, medium, and method | |
| CN108742669A (en) | The clinostatism image-forming correction method and X-ray machine of X-ray machine | |
| JP4795723B2 (en) | Digital X-ray tomography apparatus | |
| JP5768932B2 (en) | Radiography equipment |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C06 | Publication | ||
| PB01 | Publication | ||
| C10 | Entry into substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| CF01 | Termination of patent right due to non-payment of annual fee |
Granted publication date: 20130605 Termination date: 20161012 |
|
| CF01 | Termination of patent right due to non-payment of annual fee |